Ventricular assist device and method

ABSTRACT

An intracorporeal device is provided for supporting heart function of a patient. The intracorporeal device is configured to be secured across at least two anatomical walls of the heart. The intracorporeal device is configured to be secured to one or more anatomical walls by a connector. The connector is arranged to be positioned across one or more anatomical walls.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.15/582,037, filed Apr. 28, 2017, the entire contents of which areincorporated herein by reference.

FIELD OF THE INVENTION

The present invention generally relates to the field of medical devicesand surgery devices. More specifically, the invention relates to acatheter and corresponding methods of use of the catheter. The presentinvention is particularly useful in the context of minimally invasivetranscatheter and/or percutaneous procedures, such as those described inPCT Application No. PCT/EP2015/055578, entitled “PERCUTANEOUS SYSTEM,DEVICES AND METHODS” filed 17 Mar. 2015 and expressly incorporatedherein by reference in its entirety.

BACKGROUND

In PCT/EP2015/055578, the Inventor describes an intracorporeal connectorfor fluid communication between a first and a second anatomicalcompartment, in particular a ventricular assist system for allowingblood flow between the left atrium and the aorta of a patient. Thesystem is implanted across the roof of the left atrium and the aorticwall and generally comprises two main components, namely an anchor orconnector element and a fluid regulation device such as a pump.

The ventricular assist system is preferably delivered and implantedusing a transcatheter system as described for example in PCT ApplicationNo. PCT/EP2015/055578, or in PCT/EP2016/082889 entitled “TRANSCATHETERINSERTION SYSTEM” filed on 29 Dec. 2016; PCT Application No.PCT/EP2017/050275 entitled “CONNECTOR AND METHOD FOR COUPLING ANATOMICALWALLS” filed on 6 Jan. 2017, and U.S. application Nos. U.S. Ser. No.15/288,642 and U.S. Ser. No. 15/288,738 filed on 7 Oct. 2016, allincorporated herein by reference.

The connector element comprises a proximal portion, an intermediateportion and a distal portion. The proximal portion comprises a pluralityof arms which, in a working configuration, lie against the wall of thefirst compartment; the intermediate portion comprises a fluid conduitand, in a working configuration, is positioned across the anatomicalwalls; the distal portion comprises a plurality of arms which, in aworking configuration, lie against the aortic wall. The intermediateportion is adapted and configured to keep the two anatomical walls toremain in contact with each other; while the distal and proximal armsare adapted and configured to maintain the structural integrity of theanatomical walls. This is particularly important as the connector isadapted and configured to safely support the fluid regulation deviceacross the anatomical walls, which will be under pressure andsusceptible to dislodgment due to e.g. the structure of the fluidregulation device itself, blood flow created by the pump and patientmovements.

While the above ventricular assist system can be safely implanted andfluid flow successfully established, the size and structure of the heartis such that there has been a need to adapt the fluid regulation deviceand consequently the delivery and implantation methods and systems. Thefluid regulation device would typically comprise a pump element, a motorelement, and optionally a battery element (as described for example inPCT Application No. PCT/EP2016/069159 filed on 11 Aug. 2016) and, ifrequired, means for recharging said battery. Space and manipulationwithin the heart is limited and miniaturisation can only be consideredinsofar as the efficiency of the fluid regulation device is notnegatively affected. As the size of the device increases, more pressureis exerted on the anatomical walls, the integrity of which could becomecompromised. There is therefore a risk of heart tissue trauma, whichdangerous and potentially be lethal to the patient.

It is an object of this invention to mitigate problems such as thosedescribed above.

SUMMARY OF THE INVENTION

According to a first aspect, there is provided a method for supportingheart function of a patient comprising the step of securing anintracorporeal device across at least two anatomical walls of the heart,wherein at least one anatomical wall is an intra-cardiac wall and aleast one anatomical wall is an extra-cardiac wall.

Thus, the intracorporeal device is safely secured to the heart using atwo-point anchoring system. The device is stabilised and the pressureexerted by the device and blood flow onto the heart structure is sharedso that the risk of strain and trauma to a single wall is reduced.

Within the context of the invention, “intracorporeal” means inside thepatient's body and “extracorporeal” means outside the patient's body.For example, an intracorporeal device or component will be locatedwithin the patient's body, while an extracorporeal device or componentwill be located outside the patient's body.

Within the context of the invention, “intra-cardiac” means inside theheart and “extra-cardiac” means between the inside and the outside ofthe heart or outside the heart. For example, an intra-cardiac wall is ananatomical wall located inside the heart. Examples of intra-cardiacwalls include, but are not limited to the atrial septum between theright and left atria and the interventricular septum between the rightand left ventricles. An extra-cardiac wall can be an anatomical wallbetween the inside and the outside of the heart for example the wallbetween the inside of the left atrium, of the right atrium, of the leftventricle or of the right ventricle and the outside of the heart andalso the aortic wall.

In a preferred embodiment, the intra-cardiac wall is the atrial septumand the extra-cardiac wall is the wall of the left atrium, mostpreferably, the roof of the left atrium. These anatomical walls areparticularly advantageous when a fluid regulation device is to beimplanted, which regulates the flow of fluid from the left atrium to theaorta. For example, in PCT/EP2015/055578, the fluid regulation device isinserted through a puncture through the atrial septum, then implantedacross the roof of the left atrium so that blood flows through inletspositioned in the left atrium to outlets positioned in the aorta. Theleft atrium and aortic walls are subjected to tension due to theimplantation of the fluid regulation device itself and to pressure dueto the fluid flow. By providing a second anchoring point, e.g. acrossthe atrial septum, the device is stabilised and the anatomical walls areindividually subjected to less pressure. Thus, the risk of injury,trauma and leak is minimised. The atrial septum is preferred in that itis generally rigid and robust enough to secure and support anintracorporeal device but flexible enough to buffer for any movementduring and post-implantation. In addition, the atrial septum is oftenused as an insertion path and can be used as a second anchoring pointwithout the need for further puncture.

Preferably, the method further comprises the step of securing theintracorporeal device across at least a third anatomical wall. Morepreferably, the third anatomical wall is a wall adjacent to theextra-cardiac wall. Within the context of the invention, “adjacent wall”means a “wall naturally physically close”. For example, two adjacentwalls may be the adjacent walls of two adjacent anatomical compartments,such as the wall of the left atrium and the aortic wall. In a preferredembodiment, the third anatomical wall is the aortic wall adjacent to theroof of the left atrium.

The present invention is particularly useful when the flow of fluid isto be established between two anatomical compartments separated by atleast two anatomical walls. As described in PCT/EP2015/055578, theanatomical walls are pushed into contact with each other by means of adelivery catheter or outer sheath, punctured and secured together forexample using a connector. When two anchoring points are provided, thepressure and tension is spread and are no longer focused on and aroundthe connector.

Preferably, the intracorporeal device comprises a proximal portionintended to be positioned in a first anatomical compartment, anintermediate portion intended to be positioned in a second anatomicalcompartment, a distal portion intended to be positioned in a thirdanatomical compartment. In a preferred embodiment, the proximal portionof the intracorporeal device is intended to be positioned in the rightatrium, the intermediate portion is intended to be positioned in theleft atrium and the distal portion is intended to be positioned in theaorta. The intracorporeal device can therefore be secured to the atrialseptum (between the proximal and the intermediate portion) and to thewall of the left atrium and aortic wall (between the intermediateportion and the distal portion).

The position of the various elements of the intracorporeal device may beadapted and configured to assist fluid flow between any two compartmentsas will be described below in more details. In a preferred embodiment,the intracorporeal device is a fluid regulation device for assistingfluid flow from the second to the third compartment, e.g. from the leftatrium to the aorta.

Preferably, the intracorporeal device is secured to one or moreanatomical walls by means of a connector. More preferably, the connectormay be a separate connector or may be integrally formed or attached tothe intracorporeal device.

Preferably, the connector comprises a neck intended to be positionedacross one or more anatomical wall(s), a first plurality of armsextending from a first end of the neck, and a second plurality of armsextending from the second end of the neck. As described in theapplicant's previous applications cited herein, the arms are preferablymovable from a transcatheter delivery configuration (e.g. in line withthe neck) to a working configuration (e.g. substantially perpendicularto the neck).

In the case of a separate connector, the connector and/or theintracorporeal device comprise means for coupling the intracorporealdevice to the connector.

Preferably, the connector is integrally formed or coupled to theintracorporeal device. In this embodiment, the connector will comprisemeans for connecting the intracorporeal device to the anatomicalwall(s). For example, the intracorporeal device may comprise a pluralityof arms extending from the intracorporeal device. Preferably, the armsare preferably movable from a transcatheter delivery configuration (e.g.in line with the neck) to a working configuration (e.g. substantiallyperpendicular to the neck).

In a preferred embodiment, the intracorporeal device comprises a meansfor fixing the intracorporeal device to the connector. Preferably thefixing means comprises a plurality of arms extending from theintracorporeal device, preferably the distal end of the intracorporealdevice. The arms may be moved from delivery configuration (e.g.extending substantially longitudinally from the intracorporeal device)to a working configuration (e.g. extending away from the longitudinalaxis of the intracorporeal device). In the working configuration, thefixing arms may cooperate with the connector to anchor theintracorporeal device to the anatomical walls. In addition, the fixingarms may serve as additional support to the wall tissue, against thefluid flow and/or the intracorporeal device's own weight and bulk.

Preferably, the intracorporeal device comprises one or more recessesadapted and configured to receive one or more anatomical walls. In apreferred embodiment, the intracorporeal device comprises an elongatedhousing or a substantially cylindrical housing. The intracorporealdevice may comprise a circumferential recess adapted to receive theanatomical wall(s) therein, thereby securing the intracorporeal deviceto the wall. Preferably, to facilitate the insertion of the anatomicalwall(s) into the recesses, the recesses have slopped or curved walls.

According to a second aspect of the invention, there is provided anintracorporeal device for supporting heart function of a patient,wherein said device is adapted and configured to be secured across atleast two anatomical walls of the heart.

Preferably, the at least one anatomical wall is an intra-cardiac walland a least one anatomical wall is an extra-cardiac wall.

Preferably, the intracorporeal device is adapted and configured to besecured to one or more anatomical walls by means of a connector, saidconnector being integrally formed or coupled to the intracorporealdevice.

Preferably, the intracorporeal device is adapted and configured to besecured to one or more anatomical walls by means of a connector and afixing means, said connector being arranged to be positioned across oneor more anatomical walls and said fixing means being integrally formedor coupled to the intracorporeal device.

Preferably, the fixing means comprises a plurality of arms extendingfrom the intracorporeal device, for example the distal end of theintracorporeal device.

Preferably, the intracorporeal device comprises one or more recessesadapted and configured to receive one or more anatomical walls.

Preferably, the intracorporeal device comprises a proximal portionintended to be positioned in a first anatomical compartment, anintermediate portion intended to be positioned in a second anatomicalcompartment, a distal portion intended to be positioned in a thirdanatomical compartment.

Preferably, the intracorporeal device comprises a motor located in theproximal portion. Preferably, the intracorporeal device comprises one ormore fluid inlet ports in the intermediate portion. Preferably, theintracorporeal device comprises a pump in the intermediate portion.

Preferably, the pump comprises an impeller and a pump housing, whereinthe impeller is positioned within the pump housing. The impeller is arotatable element that accelerates fluid outwards from the centre ofrotation in a direction parallel to the impeller's major (longitudinal)axis, which is generally referred to as an axial flow impeller. Theimpeller rotates about its major axis with respect to the pump housing.The impeller is surrounded by the pump housing so that the rotationalvelocity of the impeller transfers into pressure when the outwardmovement of the fluid is confined by the pump housing.

Preferably, the impeller comprises a tapered profile. The taperedprofile increases from the proximal portion end to a mid portion of theimpeller, wherein the tapered profile then decreases towards the distalportion end such that the cross section of the tapered impellerapproximates an ellipse, wherein the major axis of the ellipse isparallel to the major axis of the pump housing. The tapered profile ofthe impeller has an advantage of increasing fluid pressure in the pumphousing. Thus fluid, such as blood, spends less time around parts of thedevice that generate heat, such as the motor and various bearings withinthe intracorporeal device. This reduces the probability of the fluidbeing damaged by heat generated by the device, which in turn reduces theprobability of the fluid clotting and blocking the circulatory system.Thus fluid cools the surface of the motor housing and the internal pumpelements.

Preferably, the intracorporeal device comprises one or more fluid outletports in the distal portion. One or more fluid inlet ports may bepositioned in the proximal and/or intermediate portion depending on thecompartments the fluid flows from/to. In a preferred embodiment, theproximal portion of the intracorporeal device is intended to bepositioned in the right atrium, the intermediate portion is intended tobe positioned in the left atrium, and the distal portion is intended tobe positioned in the aorta. In a most preferred embodiment, theintermediate portion comprises one or more inlet ports and the distalportion comprises one or more outlet ports so that fluid can flow fromthe left atrium to the aorta.

Preferably, the length of the intermediate portion and the distalportion is designed such that the one or more fluid inlet ports in theintermediate portion are positioned in the left atrium and the one ormore fluid outlet ports in the distal portion are positioned in theaorta.

Preferably, the intracorporeal device comprises a static diffuserpositioned in the distal portion of the intracorporeal device.Preferably, the diffuser is positioned between the impeller and the oneor more fluid outlet ports. Preferably, the diffuser is coupled to anend of the impeller via a bearing. Preferably, the diffuser is fixedlyattached to the interior of the pump housing such that the diffuser isnot able to rotate. Preferably, the diffuser and bearing support theimpeller and allow the impeller to rotate about its major axis, whilstthe diffuser remains fixed to the interior of the pump housing. Thediffuser has an advantage of increasing fluid diffusion from the outletof the device due to the angle and profile of the blades of thediffuser.

Preferably, the intracorporeal device comprises a fixing means that isarranged to secure the intracorporeal device to an anatomical wall.Preferably, the fixing means is at an end of the distal portion of theintracorporeal device.

Preferably, in use, the connector is positioned through the roof of theleft atrium and the aortic wall. Preferably, the neck of the connectorand/or the distal portion of the intracorporeal device form apericardial seal. Preferably, the neck of the connector acts as adocking means to assist in coupling the distal portion of theintracorporeal device across the anatomical walls and with respect tothe connector.

The fixing means may be a type of anchor/support member with a number ofarms/tissue support members that can deploy against the wall of theaorta for example. This may position and secure the distal portion ofthe device with respect to the aorta to allow for efficient fluidtransfer through the device.

Preferably, the intracorporeal device comprises a static diffuserpositioned at an end of the distal portion. This has the advantage offurther increasing fluid diffusion at an outlet of the device becausethe fixed blades aid in fluid diffusion. This also has the advantage offacilitating easier deployment of the device because a guide wire and/orballoon may be attached to a guide wire holder on the static diffuser toenable accurate positioning within the human body.

Preferably, the intracorporeal device comprises a motor coupling elementthat is arranged to couple a drive shaft of the motor to the pump.Preferably, the motor coupling element is positioned between the motorand the impeller. Preferably, the motor coupling element magneticallycouples the drive shaft of the motor to the pump. This has an advantageof maintaining a hermetic seal of the motor and drive shaft with respectto fluid within the circulatory system, whilst also enabling the motorand drive shaft to be easily removed from the remainder of theintracorporeal device. Thus components of the intracorporeal device thatare most likely to need removal, modification or replacement, e.g. themotor, can be detached and replaced easily whilst maintaining theremainder of the intracorporeal device in position within the body.

Preferably, the motor coupling element axially couples the drive shaftof the motor to the pump. This has an advantage of simplifying thecoupling between the drive shaft of the motor and the pump, whilstmaintaining a hermetic seal between the motor and fluid within the body.

Preferably, the motor coupling element radially couples the drive shaftof the motor to the pump. Preferably, a portion of the motor couplingelement surrounds and magnetically couples to an elongate portion of themotor that houses the motor drive shaft. This has an advantage ofincreasing the torque transfer between the drive shaft and the pumpimpeller. Radial configuration of the coupling magnet forces eliminatesadditional bearing loading and heat generated by friction.

Preferably, the motor, the drive shaft, and a magnetic element at an endof the drive shaft are situated in a hermetically sealed housing. Thishas an advantage of allowing the motor to be positioned in thecirculatory system. If the elements discussed above were not situated ina hermetically sealed housing, fluid within the circulatory system woulddamage these elements and/or the elements may cause contamination to thefluid within the circulatory system.

Preferably, a portion of the motor coupling element partially surroundsa portion of the hermetically sealed housing containing the magneticelement. This has an advantage of facilitating radial magnetic couplingand allowing fluid to flow between the motor coupling element and theportion of the hermetically sealed housing.

Preferably, an interstitial space/void is present between the portion ofthe motor coupling element and the portion of the hermetically sealedhousing. This has an advantage of facilitating fluid flow in theinterstitial space to prevent fluid damage.

Preferably, an interface of the motor coupling element is magneticallyfixable to an interface of the motor in order to couple the motor driveshaft to the pump, and wherein a fluid inlet is defined between saidinterfaces during coupling. This has an advantage of facilitating fluidflow between the interfaces so that fluid can enter the interstitialspace between the interfaces.

Preferably, a further interface of the motor coupling element couples toan interface of the impeller. This has an advantage of translatingmovement of the motor drive shaft to the impeller.

Preferably, the motor coupling element comprises one or more boreportions. This has an advantage of allowing fluid that has entered theinterstitial spaces to exit the motor coupling element. This results inwashing of a bearing inside of the motor coupling element, without thefluid temperature increasing to a point where the fluid becomes damaged.

Preferably, the one or more bore portions are bore holes and/orsegmented arms that couple the interfaces of the motor coupling elementto the respective impeller interfaces.

Preferably, in use, fluid is arranged to flow between the motorinterface and the interface of the motor coupling element and throughthe one or more bore portions towards the impeller. This has anadvantage of reducing heat in the bearing and preventing the fluid frombeing damaged by excess heat.

Preferably, the one or more fluid inlet ports are positioned between theone or more bore portions and the impeller in the intermediate portionof the pump housing. This has an advantage of allowing fluid exitingfrom the bore portions to mix with fluid entering the fluid inlet ports.Thus any excess heat absorbed by the fluid exiting the bore portions canbe dissipated efficiently with fluid entering via the fluid inlet ports.

Preferably, the intracorporeal device comprises power and control means.Preferably, the control means is coupled to the motor via a taperedportion. The tapered portion has an advantage of reducing strain on theconnector between the motor and the power and control means. Preferably,the tapered portion reduces in dimension as it tapers away from theproximal portion of the intracorporeal device.

Within the context of the invention, the terms “proximal” and “distal”are used relative to the medical professional, e.g. the proximal end isthe end nearest the medical professional and the distal end is the partof the device that is inserted first into the patient.

Within the context of the invention, transcatheter includespercutaneous, trans-atrial, trans-femoral (through the leg),trans-apical (in the chest between the ribs), and trans-aortic (in theupper chest). Preferred embodiments are percutaneous systems, devicesand methods.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be further described with reference to the drawingsand figures, in which:

FIGS. 1, 1A, and 1B illustrate a method according to the presentinvention using a first intracorporeal device;

FIG. 2 illustrates a method according to the present invention using asecond intracorporeal device;

FIG. 3 is a schematic representation of an intracorporeal deviceincorporating fixing means and control means according to the presentinvention;

FIG. 4 is a schematic representation of the intracorporeal device fromFIG. 3 without fixing means.

FIG. 5A is a schematic representation of an outer view of anintracorporeal device without fixing means or control means.

FIG. 5B is a schematic representation of an internal view of theintracorporeal device without fixing means or control means.

FIG. 5C is a schematic representation of a static diffuser utilised inthe intracorporeal device in FIGS. 5A and 5B.

FIG. 5D is a schematic representation of an alternative impeller.

FIG. 6A is a schematic representation of a cross section of anintracorporeal device utilising radial coupling between a motor and amotor coupling element.

FIG. 6B is a schematic representation of a cross section of anintracorporeal device utilising axial coupling between a motor and amotor coupling element.

FIG. 7 is a schematic representation of segmented arms from the motorcoupling element.

FIG. 8 is an exploded schematic representation of constituent elementsof an intracorporeal device.

DETAILED DESCRIPTION

The invention is described by way of examples, which are provided forillustrative purposes only. These examples should not be construed asintending to limit the scope of protection that is defined in theclaims. For example, although various aspects have been described withrespect to the heart and the circulatory system, this is not intended tobe limiting, and is merely performed to provide an example ofimplementation. Aspects disclosed herein may be utilised in any medicaldevice implantable within the human body, for example in thecardiovascular system, respiratory system, gastric system, neurologicalsystem, and the like, some examples including implantable pumps and drugdelivery pumps. As used herein, the term “means” can be equivalentlyexpressed as, or substituted with, any of the following terms: device,apparatus, structure, part, sub-part, assembly, sub-assembly, machine,mechanism, article, medium, material, appliance, equipment, system, bodyor similar wording.

Referring to FIG. 1, there is illustrated a method according to thepresent invention for supporting heart function of a patient comprisingthe step of securing an intracorporeal device 1 across at least twoanatomical walls of the heart, wherein at least one anatomical wall isan intra-cardiac wall and a least one anatomical wall is anextra-cardiac wall.

In this example, the intracorporeal device 1 is secured across theatrial septum 2 (an intra-cardiac anatomical wall), the roof of the leftatrium 3 (an extra-cardiac anatomical wall) and the aortic wall 4 (i.e.a third anatomical wall). The intracorporeal device 1 comprises aproximal portion 5 located in use in the right atrium RA, anintermediary portion 6 located in use in the left atrium LA, and adistal portion 7 located in use in the aorta. A power and control cable16 is coupled to an end of the proximal portion 5.

The intracorporeal device 1 is substantially cylindrical or comprises asubstantially cylindrical housing. A motor M is located in the proximalportion 5 and a pump P is located in the intermediate portion 6. Theposition of the fluid inlet and outlet ports may be adjusted so that thefluid inlet ports are formed in the first fluid feeding compartment andthe fluid outlet ports are formed in the second fluid receivingcompartment. In this example, the fluid inlet ports 8 are formed in theintermediate portion 6 positioned in the left atrium LA and the fluidoutlet ports 9 are formed in the distal portion 7 positioned in theaorta AO.

In an alternative implementation, the motor 5 may be housed in theintermediate portion 6. As a result, the proximal portion 5 is no longerrequired and is no longer situated in the right atrium. Thus only apower and control cable would be present in the right atrium.

In FIG. 1, the intracorporeal device 1 comprises a circumferentialrecess 10 between its proximal and intermediate portions 5,6. The shapeand dimensions of the recess are such that the atrial septum can bereceived into the recess 10. The recess 10 may have sloped or curvedwalls as shown in FIGS. 1A and 1B, respectively, to facilitate theinsertion of the atrial septum 2 into the recess 10.

Where the intracorporeal device 1 is to be secured to a singleanatomical wall (e.g. the atrial septum 2) then a recess 10 may besufficient. However, when the intracorporeal device 1 is to be securedacross two or more anatomical walls (e.g. the wall of the left atriumand the aortic wall 4), then a connector 11 may be preferred. Theconnector 11 shown in FIG. 1 is a separate connector.

Connectors suitable for use in the context of the present invention aredescribed in detail in PCT/EP2017/050275, U.S. Ser. No. 15/288,642 andU.S. Ser. No. 15/288,738. The connector 11 generally comprises a neck 13for fluid passage between two anatomical compartments, positioned in useacross/through the anatomical walls 3,4; a first plurality of armsand/or blades 15 extending from the distal end of the neck 13 and lyingin use against the wall of the receiving compartment and a secondplurality of arms and/or blades 14 extending from the proximal end ofthe neck 13 and lying in use against the wall of the feedingcompartment. The arms and/or blades are preferably integrally formed orsecured to the distal end of the neck 13. In use, the arms and/or bladesrest partially or wholly against the anatomical walls 3, 4. The neck 13also supports the intracorporeal device 1 when it is positioned acrossthe anatomical walls 3, 4. In use, (part of) the distal portion 7 on theintracorporeal device 1 is positioned through the neck 13 of theconnector 11, and thus across the anatomical walls 3, 4. For example,the intracorporeal device may include a recess to receive the neck ofthe connector. The dimensions of the neck 13 and the distal portion 7 ofthe intracorporeal device 1 are arranged such that coupling the distalportion 7 with the neck 13 forms a pericardial space seal. Thus the neck13 facilitates a seal as well as facilitating pump docking and supportof the intracorporeal device 1.

Upon removal of the intracorporeal device from connector 11, theconnector 11 forms a seal between the anatomical walls 3, 4 to preventfluid diffusing between the two regions defined by said walls 3, 4.

This specific configuration secures the connector 11 to the anatomicalwalls 3,4 and enables the connector 11 to maintain the anatomical walls3,4 in contact with each other while supporting the integrity of theanatomical walls 3,4. Thus the arms and/or blades act as tissuesupporting members in order to support the integrity of the anatomicalwalls 3,4.

The intracorporeal device 1 may be provided with one or more recessese.g. a circumferential recess to receive the neck 13 of the connector 11therein.

Other means for securing the intracorporeal device 1 to the anatomicalwall(s) 2,3, 4 are envisaged, including but not limited to tabs, hooks,arms, cushions, high friction surfaces, biologically active covering,and the like.

Referring to FIG. 2, there is illustrated an alternative method ofsecuring the intracorporeal device 1 with respect to the connector 11.Previously, referring to FIG. 1, the distal portion 7 of theintracorporeal device was coupled through/to the neck 13 of theconnector 11, e.g., via frictional force or through the compression ofconnector 11 (i.e. connector 11 is preferably made of anexpandable/compressible material). Alternatively or in combination, anumber of tissue support/fixing members 12 may be coupled to the distalportion 7 of the intracorporeal device 1. These tissue support/dockingmembers 12, when deployed, contact the aortic wall and further supportthe intracorporeal device 1 with respect to the connector 11. Thus acombination of the connector 11 and the tissue support/docking members12 enable enhanced support as well as the ability to easily couple andde-couple the distal portion 7 of the intracorporeal device 1 withrespect to the connector 11.

Referring to FIG. 3, there is illustrated a schematic representation ofan intracorporeal device 300 with associated fixing means 302 andcontrol means 304. The fixing means 302 in this embodiment relates tothe tissue support/docking members 12 described in relation to FIG. 2.The fixing means 302 comprise a coupler 330 attached to a proximal endof the fixing means 302. A number of pump docking members/support arms306 are attached to a distal (opposite) end of the fixing means 302.FIG. 3 illustrates the fixing means 302 in a “deployed” position,wherein the number of pump docking members/support arms 306 are splayedout substantially perpendicular to the longitudinal axis of theintracorporeal device 300. These pump docking members/support arms 306,in use, abut a portion of the anatomical wall 4 (see FIG. 1,2), forexample the aortic wall, in order to position and secure theintracorporeal device 300 between the anatomical walls 3, 4 (see FIG.1,2) and inside the neck 13 of the connector 11.

The number of pump docking members/support arms 306 act as a tissueshield and pump protector, since the wall of the aorta is held away fromthe intracorporeal device 300 that is positioned inside the aorta. Thenumber of pump docking members/support arms 306 distribute pressure sothat each individual docking member/arm does not damage the anatomicalwall 4.

If the intracorporeal device 300 needs to be removed from across theanatomical walls 3, 4, the pump docking members/support arms 306 arere-positioned into a “delivery” position, wherein the pump dockingmembers/support arms 306 are arranged substantially parallel with thelongitudinal axis of the intracorporeal device 300 to enable said deviceto be removed from the neck of the connector 11 (see FIG. 2). This hasan advantage of allowing the intracorporeal device 300 to be removedwithout damaging the anatomical walls 3, 4, which are protected by theconnector 11. On removal of the intracorporeal device 300, the connector11 seals the space between the anatomical walls, 3, 4 until theintracorporeal device 300 is re-inserted.

In a preferred embodiment, the delivery of the intracorporeal device 300is via echo guided trans-septal and/or trans-aortic methods for thespecific puncture sites, wherein echo planes may be used for allpuncture sites. An echo plane is a defined projection/view where anatomyand angles are predefined so as to visualise specific regions ofinterest in a specific way. The echo guided methods may be, for example,intra-cardiac, trans-esophageal, or trans-thoracic.

The coupler 330 is positioned over a crown connector/coupling member(not visible) of the intracorporeal device 300 and abuts an end portion332 of the intracorporeal device 300.

The control means 304 comprise a drive-line 308 that houses cabling topower and/or control the intracorporeal device 300. In this example, thecontrol means 304 is coupled to a proximal portion 310 of theintracorporeal device 300 via a tapered portion 312. The tapered portion312 tapers in size away from the proximal portion 310 of theintracorporeal device 300. The tapered portion 312 has an advantage ofreducing strain on the connector interface (not shown) that is housed inportion 314 between the proximal portion 310 and the tapered portion312. The connector interface couples the cabling in the control means304 to the motor 316. The motor 316, connector interface and controlmeans 304, form a hermetically sealed unit, which is arranged to preventfluid ingress.

A portion of the motor 316 is situated within a rear portion 318 of thepump housing 320. The rear portion 318 of the pump housing 320 defines anumber of washing holes 322, also called bore portions, that enablefluid, such as blood, to flow through the rear portion 318 of the pumphousing and between a driving portion (not shown) of the motor 316 and amotor coupling element 324, which is partially visible in this figure.Fluid inlets 326 are arranged in the rear portion 318 of the pumphousing 320. Between the fluid inlets 326 and the fixing means 302 is animpeller (not shown) situated within a front portion 328 of the pumphousing 320.

The crown connector/coupling member (not shown) acts as a main outletfor fluid of the intracorporeal device 300. A static diffuser 305(partially visible), inside of the crown connector/coupling member,interferes with the flow of fluid to generate a desired fluid flow outof the main outlet and into the aorta. The crown connector/couplingmember comprises one or more fluid outlet ports 303.

In some other embodiments, for example the embodiment of FIG. 1, thefixing means 302 may be dispensed with. In these embodiments, the crownconnector/coupling member may also be dispensed with. Thus the diffuser305 may be situated within the distal end of the front portion 328 ofthe pump housing 320, rather than inside the crown connector/couplingmember.

In this example, the distal portion of the intracorporeal device 300comprises the fixing means 302 and crown connector/coupling member (notshown), wherein in use the distal portion is situated within the aorta.The intermediate portion of the intracorporeal device 300 comprises thepump housing 320 with its associated elements such as the impeller, andmotor coupling element 324. The proximal portion of the intracorporealdevice 300 comprises the portion of the motor that is not within thepump housing 320, the portion 314, tapered portion 312, and controlmeans 304.

Referring to FIG. 4, the intracorporeal device 300 from FIG. 3 isillustrated without fixing means 302 coupled to the intracorporealdevice. Thus in this example, the crown connector/coupling member 331can be viewed in more detail. The crown connector 331 comprises thestatic diffuser 305 that is coupled to the side walls of the crownconnector 331. The diffuser comprises static blades 404 and a guide wireholder 402. In use, fluid flows over the static blades 404 of the staticdiffuser 305, wherein the blades are orientated so to affect theorientation of fluid as it flows through the crown connector 331 to theone or more fluid outlet ports 303. The guide wire holder 402 alsoallows enhanced guide wire connectivity and/or balloon connectivity. Forexample, a guide wire (not shown) can be threaded through guide wireholder 402 to enable the intracorporeal device 300 to be accuratelypositioned within the human body via, for example, a catheter basedimplantation method.

In some examples, the crown connector 331 may be dispensed with and thestatic diffuser 305 may be positioned at a front portion 328 of the pumphousing 320.

Referring again to FIG. 4, the portion 314 is illustrated so thatconnector interface 406 can be viewed. Connector interface 406electrically couples the control means 304 to the back end of the motor.This enables power and/or control of the motor 316. Tapered portion 312reduces strain on the connector interface 406. This is particularlyimportant in the present invention because the intracorporeal device 300needs to maintain flexibility. This is because in use the intracorporealdevice 300 is implanted within the left and right atrium of the heartand the aorta via a catheter based insertion system. As such, theintracorporeal device needs to be flexible enough to follow thedirection of the arterial system. Portion 314 maintains the hermeticseal of the motor 316, whilst allowing coupling of the control means 304to the motor 316 so that the motor can be implanted within thecirculatory system of the human body.

Referring to FIG. 5, there is illustrated a schematic representation ofan intracorporeal device 500. In this example, power and control meansare not illustrated. Further, in this example, the intracorporeal device500 is illustrated without fixing means 302 or a crownconnector/coupling member 331. Thus a diffuser 534 is situated at theoutlet 503 of the intracorporeal device 500 rather than in the crownconnector/coupling member 331, as illustrated in FIGS. 3 and 4.

FIG. 5A illustrates an outer view of the intracorporeal device 500,whilst FIG. 5B illustrates an internal view of the intracorporeal device500. FIG. 5C illustrates the diffuser 534 and FIG. 5D illustrates analternative impeller design.

Intracorporeal device 500 in FIG. 5A comprises motor 502 and pumphousing 504. A portion of the motor 502 is situated within the pumphousing 504. The intracorporeal device in FIG. 5A comprises a proximalportion 506, an intermediate portion 508 and a distal portion 510, asdiscussed previously.

The portion of the pump housing 504 that contains the portion of themotor comprises a number of bore portions, which may also be washingholes/slits 512. Pump housing 504 further comprises a number of fluidinlets 514.

Referring to FIG. 5B, it can be seen that there is an interstitial space516 between the motor 502 and a motor coupling element 518. The dottedline represents part of the motor 502 that extends inside the motorcoupling element 518. In this example, this part relates to ahermetically sealed motor drive shaft 520. A bearing 522 couples thehermetically sealed motor drive shaft 520 to the motor coupling element518. The hermetically sealed motor drive shaft 520 inside the motorcoupling element 518 is of a smaller diameter than the motor couplingelement 518, wherein the motor coupling element 518 is suspended aroundthe hermetically sealed motor drive shaft 520 with the assistance of thebearing 522 and a magnetic field that is generated due to one or moremagnetic elements on the motor drive shaft 520 and in the motor couplingelement 518. In this example, the hermetically sealed motor drive shaft520 inside of the motor coupling element 518 comprises a magnet orseries of magnets (not shown) of a first polarity. The motor couplingelement 518 comprises a magnet or series of magnets of a secondpolarity, wherein the first and second polarities are different. Thus aninterstitial space is maintained between the portion of the hermeticallysealed motor drive shaft 520 inside the motor coupling element 518 andthe portion of the motor coupling element 518 that surrounds thehermetically sealed motor coupling element 518. This can be betterunderstood from FIG. 6.

Magnetic coupling between the magnet on the motor drive shaft 520 andthe motor coupling element 518 has an advantage that movement of themotor drive shaft 520 can be replicated by the motor coupling element518 without the motor drive shaft 520 being exposed to fluid. Again,this feature can be better understood from FIG. 6. This allows thehermetic seal of the motor 502 to be maintained, allowing operation in afluidic environment.

A further advantage of the magnetic coupling between the magnet on themotor drive shaft 520 and the motor coupling element 518 is that themotor 502, and any associated control means (not shown, see 304 fromFIGS. 3 and 4), can be disconnected from the remainder of theintracorporeal device 500 when the device is situated within the body.Thus parts of the intracorporeal device 500 that are more likely torequire removal, replacement, or modification, such as the motor 502 andcabling, can be removed and replaced, whilst keeping the pump housing504 and associated elements such as the motor coupling element 518 inposition in the body. This has an advantage of reducing movement andre-positioning of the pump housing 504, which may be positioned betweenanatomical walls of a patient's heart, such as the left and right atriumand aorta. Routine movement and/or re-positioning of the pump housing504 with respect to the anatomical walls of a patient's heart may insome circumstances include risk of damage to said anatomical walls.

In this example, a number of segmented arms 524 surround the bearing522. Interfaces of the segmented arms 524 couple the motor couplingelement 518 to an impeller 526. Thus movement of the magnet on the motordrive shaft 520 can be translated to the impeller 526 without the driveshaft, or any other direct connection, of the motor 502 being coupleddirectly onto the impeller 526. The segmented regions between the arms524 enable fluid to flow from the interstitial space 516 and to joinfluid being forced through the impeller 526, via the segmented arms 524.

In another example, the segmented arms 524 may be replaced by one ormore bore holes in the motor coupling element. The bore holes andsegmented arms may collectively be referred to as bore portions.

There are several advantages of the arrangement of the motor 502 and themotor coupling element 518, which will now be discussed. Duringoperation, the bearing 522 will generate heat as it supports movement ofthe motor coupling element 518 with respect to the hermetically sealedmotor drive shaft 520. Fluid can flow through the interstitial space 516between the motor 502 and the motor coupling element 518 to cool thebearing 522. The segmented arms 524, and/or bore holes, enable fluid toflow away from the bearing 522. Thus fluid can flow through washingholes 512 and into the interstitial space 516, cool the bearing 522 andmix with fluid being drawn into the impeller 530 via the fluid inlets514. This enables cooling of the bearing 522, without the fluidincreasing significantly in temperature to a point where it can becomedamaged. Without the segmented arms 524 or bore holes, fluid, such asblood, would not be able to easily flow past the bearing 522. Thus heattransferring from the bearing 522 to the fluid could cause the fluid toincrease in temperature and become damaged. A two degree temperaturerise in blood can cause blood damage and/or clotting. These clots couldbecome dislodged and move around the circulatory system causingundesirable blockages.

In another example, the segmented arms 524 may be joined together toform a continuous arm. In this example, one or more bore holes may bepresent to enable fluid flow out of the motor coupling element 518.

Preferably the bearing 522 is formed from a ceramic material, which hasan advantage of increased heat and wear tolerance as well as requiringless cooling. In turn, less heat is transferred to the fluid and thusreduces localised heating of the fluid and/or surrounding tissue.

As discussed above, the impeller 526 is coupled to the motor couplingelement 518 via the segmented arms 524. In another example, wherein thesegmented arms are joined together, the impeller is coupled to the motorcoupling element 518 via the continuous arm.

During operation, the impeller 526 rotates about its axis 528 and drawsfluid into the pump housing via the fluid inlet 514 and the segmentedarms 524 (via the interstitial space 516). The impeller 526 comprises abody 530 and a number of blades 532. The blades 532 force fluid past theimpeller 526 with respect to the pump housing at a rate defined by therotational speed of the impeller 526.

Preferably, the body 530 of the impeller 526 is tapered, wherein thetaper increases from the motor coupling element 518 end to a mid regionof the impeller, before reducing again to an outlet end of theintracorporeal device 500. The tapered body is thus elliptical in shapewith respect to the longitudinal axis of the impeller. The taper of thebody 530 of the impeller 526 increases fluid pressure in the pumphousing around the impeller 526. This results in fluid spending lesstime around parts of the motor 502 that generate heat, thereby reducingblood damage/clotting in and/or around the intracorporeal device 500.

In this example, the diffuser 534 is coupled to an outlet end of theimpeller 526 via a bearing 536. The bearing 536 may be similar tobearing 522. The bearing 536 allows the impeller 526 to rotate about itsaxis whilst being supported by the diffuser 534. The diffuser 534 iscoupled to the walls of the housing 504 so that it does not rotate. Anend portion 538 of the diffuser 534 is positioned at the outlet 503 ofthe pump housing 504.

As illustrated in FIG. 5C, the diffuser 534 comprises a body 539, anumber of blades 535 coupled to the body 539, and a guide wire holder541. The guide wire holder 541 allows a guide wire and/or balloon to becoupled to the intracorporeal device 500. Preferably, the diffusercomprises four blades 535. The blades 535 vary in thickness andorientation with respect to the body 539 of the diffuser 534. The blades535 curve away from or towards the body 539. The thickness of the blades535 varies as the blades 535 move away from the body 539 of thediffuser. The thick/thin profile of the blades 535 coupled with theangle of the blades 535, allows optimal diffusion of fluid from theoutlet of the intracorporeal device 500. Thus the thickness profile andthe angle of the blades 535 are optimised to minimise blood damage andmaximise pressure generation inside the intracorporeal device 500.

A general operation of the intracorporeal device 500 will now be given.The hermetically sealed motor drive shaft 520 rotates about itslongitudinal axis, resulting in magnet(s) on the motor drive shaft andthe magnet(s) on the motor coupling element 518 also rotating withrespect to each other, which in turn rotates the impeller 526 about itslongitudinal axis, whilst the diffuser 534 remains in a fixed position.In use, the proximal portion 506 is positioned in the right atrium. Theintermediate portion 508, comprising the washing holes/slits 512 and thefluid inlets 514 are positioned in the left atrium. The distal portioncomprising the outlet of the intracorporeal device 500 is positioned inthe aorta. Thus the pump housing 504 is positioned between the wall ofthe left atrium 3 and the aortic wall 4 (see FIG. 1). A connector 11seals the wall of the left atrium 3 and the aortic wall 4 around thepump housing 504, effectively providing a fluid seal. Thus fluid, suchas blood, can only flow between the wall of the left atrium 3 and theaortic wall 4 via the intracorporeal device 500 when the device isoperating at full capacity. Impeller 530 draws fluid into pump housing504 via the fluid inlets 514, the interstitial space 516 and associatedsegmented arms 524. Fluid pressure builds up in the pump housing 514 dueto the tapered design of the body 530 of the impeller 526. The impellerblades 532 generate an axial fluid flow through the impeller 526,wherein the diffuser 534 optimally provides a flow/diffusion of fluid tothe outlet of the pump housing 504 and into the aorta. As discussedpreviously, the length of the pump housing 504 and constituentcomponents are designed such that the one or more fluid inlet ports arein the left atrium and the one or more fluid outlet ports are in theaorta.

In an example, wherein the intracorporeal device 500 is operating atpartial capacity, for example to provide partial support to a patient'sheart, there may be a partial flow of fluid, such as blood, through theleft ventricle.

Referring to FIG. 5D, an alternative impeller 550 is illustrated. Inthis example, the alternative impeller, denoted the “mixed flow”impeller 550 is illustrated coupled to the motor coupling element 518via the segmented arms 524. The mixed flow impeller 550 comprises afirst set of blades 552 and a second set of blades 554, wherein thefirst set of blades 552 are longer than the second set of blades 554.The distribution of different shaped and angled blades gives the mixedflow impeller 550 a partial radial outlet, as well as an axial outlet.Thus the mixed flow impeller generates an axial as well as a radial flowof fluid towards the outlet of the intracorporeal device 500. This hasan advantage of increasing efficiency of the intracorporeal device 500as the mixed flow impeller 550 provides higher output pressure comparedto axial flow impellers. A further advantage of the mixed flow impeller550 is that an intracorporeal device 500 utilising this impeller 550, asopposed to the impeller 530, has a reduced overall length because thereis no need for the diffuser 534.

Optionally, a diffuser that similar to diffuser 534 may also optionallybe coupled to the mixed flow impeller 550.

FIG. 6A illustrates a schematic representation of radial couplingbetween the motor and motor coupling element that may be utilised in theintracorporeal device, and FIG. 6B illustrates a schematicrepresentation of axial coupling between the motor and motor couplingelement that may be utilised in the intracorporeal device. Both FIGS. 6Aand 6B include a diffuser 634 between a main outlet of theintracorporeal device 600, 650 and the impeller 632. Thus fixing means302 and crown connector/coupling member 331 are not illustrated.

Referring to FIG. 6A, a cross section of an intracorporeal device 600 isillustrated. Motor 602 includes a motor drive shaft 604 that extendsinto a portion of the motor that is partially surrounded by a motorcoupling element 606. An end of the shaft 604 includes a first set ofmagnets 608 of a first polarity. The first set of magnets 606 are housedin a hermetically sealed unit 610 that encapsulates the magnet 606 anddrive shaft. The motor coupling element 606 partially surrounds thehermetically sealed unit 610, wherein a second set of magnets 615 of anopposing polarity are situated within the motor coupling element 606. Abearing 612 rotatably couples the motor coupling element 606 to thehermetically sealed unit 610. The opposing magnetic fields generated bythe first set of magnets 608 and the second set of magnets 615 attracteach other, and thus pull the motor coupling element 606 towards thehermetically sealed unit 610. Magnets surround the full circumference ofthe hermetically sealed unit 610 and the motor coupling element 606 suchthat there is an equal magnetic force that prevent any interfaces of thehermetically sealed unit 610 and motor coupling element 606 fromtouching, thereby generating an interstitial space between thehermetically sealed unit 610 and the motor coupling element 606. In use,fluid, for example blood, flows into interstitial space 614 between themotor 602 and the motor coupling element 606 and through theinterstitial space defined by the hermetically sealed unit 610 and themotor coupling element 606 and exits via the gaps between the segmentedarms 616. Thus the bearing 612 is “washed” with fluid, which preventsthe bearing 612 from generating excessive heat. Due to the flow of fluidfrom the interstitial space 614 to the segmented arms 616, the bearing612 does not generate localised heating or heat the fluid as it “washes”the bearing 612.

Additionally, fluid flows 617 into fluid inlets 618 and mixes with fluid619 exiting between the segmented arms 616. As discussed previously, thesegmented arms 616 may be replaced by a continuous arm having one ormore bore holes to achieve the same fluid flow effect.

In this example, the magnet 608 on the drive shaft 604 rotates along theaxis of the shaft 604, resulting in an associated rotation of the magnet615 in the motor coupling element 606. This radial coupling eliminatesaxial forces in the coupling assembly and has a higher rated torquecompared to an axially coupled device (discussed in FIG. 6B).Furthermore, the bearing 612 experiences less friction compared to anaxially coupled device.

Referring to FIG. 6B, a cross section of an axially coupledintracorporeal device 640 is illustrated, comprising a motor housingpart 650 and a pump part 651. In this example, a first magnet 652 of afirst polarity is arranged on an end of motor shaft 654 within the motorhousing part 650. A second magnet 656 of a second different polarity ispositioned opposite the first magnet in the pump part 651, whereinmovement of the shaft 654 and thus the first magnet 652 is replicated bythe second magnet 656. This form of coupling is defined as axialcoupling.

An interstitial space 670 is defined between the motor housing part 650and the pump part 651, similar as discussed with respect to FIG. 6A. Theinterstitial space allows fluid to flow 671 around a bearing 672 thatsupports the pump part 651 with respect to the motor housing part 650.

Axial coupling is simpler in design than radial coupling illustrated inFIG. 6A. This form of indirect coupling maintains a hermetic seal of themotor and allows torque transfer between the motor and impeller driveshaft 658. Further, axial coupling is simpler to manufacture because themagnetic elements are not as thin as the magnetic elements needed forradial coupling.

Referring to FIG. 7, an example of the segmented arms from FIG. 6 areillustrated. Segmented arms 702 couple the impeller 704 to the motorcoupling element 706. The regions/gaps between the segmented arms 702allow fluid to flow past and “wash” the bearing (not shown). Thus fluidcan flow in the interstitial space between the hermetically sealed motordrive shaft (not shown) and the motor coupling element 706. This has anadvantage of cooling the device and maintaining a flow of fluid toprevent damage and/or clotting. The fluid that is output from the gapsin the segmented arms 702 mixes with the fluid drawn into the pumphousing (not shown) during rotation of the impeller. The combined fluidflows through the impeller 704 in an axial manner.

Referring to FIG. 8, an exploded view of an intracorporeal device 800 isillustrated. The separate features will be put into context using thedescribed components in FIGS. 6A and 6B.

Motor 802 comprises motor shaft 803, wherein the motor shaft 803 ishoused inside hermetically sealed unit 804 and sealing conduit 806. Thehermetically sealed unit 804 corresponds to the hermetically sealed unit610 from FIG. 6A. The hermetically sealed unit 804 is hollow to enablethe motor shaft 803 and magnet (not shown) to rotate within thehermetically sealed unit. The sealing conduit 806 houses thehermetically sealed unit 804 and part of the motor coupling element 812.In this example, the sealing conduit 806 provides the gaps 614 in FIG.6A to enable fluid to enter the void between the motor coupling element606 and the hermetically sealed unit 610 from FIG. 6A.

Bearing 808 relates to bearing 612 from FIG. 6A, and is positioned suchthat it rotatably couples the hermetically sealed unit 804 to the motorcoupling element 812, thereby enabling rotation of the motor couplingelement 812 about the bearing 808 axis. Magnetic components 810 relateto the second magnet 615 situated within the motor coupling element 606from FIG. 6A. The magnetic components 810 are fixably attached to themotor coupling element 812 so that movement of the magnet withinhermetically sealed unit 804 is translated to the motor coupling element812. Impeller 814 is coupled to the motor coupling element 812 so thatmovement of the magnet within the hermetically sealed unit 804 is alsotranslated to the impeller 814. Diffuser 818 is coupled to the impeller814 via a bearing (not shown) and to the pump housing 816. The impeller814 rotates about its longitudinal axis, whilst the diffuser 818 remainsfixed. Pump housing 816 is positioned around components as illustratedwith respect to FIG. 6A.

Optionally, the bearings discussed above, for example bearing 808, maybe hydraulic bearings, or a combination of ceramic and hydraulicbearings, wherein the base of the bearing (motor side) may be ceramicand the top of the bearing (outlet side) may be hydraulic.

Optionally, the diffuser 818 may be positioned in a crownconnector/coupling member (not shown), such as the crown connector 331from FIG. 3

Although the present invention has been described with respect to a leftatrium to aorta procedure, the system and method can also be applied toother delivery sites including, but not limited to, right atrium-aorta,vena cava-pulmonary artery, vena cava-aorta. Thus, the present inventioncan be broadly applied for example as left ventricular assist devices(LVAD), right ventricular assist devices (RVAD) or biventricular assistdevices (BiVAD), for cardiopulmonary support (CPS) or forintra-corporeal membrane oxygenation (ICMO) or bubble oxygenation, forthe treatment of other organs with pressure issues (e.g. gastric orneurological procedures). The present invention is versatile and a widevariety of applications can therefore be envisaged.

Thus, from the above description, it can be seen that the presentinvention provides a connector for establishing fluid communicationbetween two anatomical compartments. The connector also enables a pumpor other medical devices to be securely implanted across one or moreanatomical walls. This can be achieved accurately and safely. Thepresent invention provides a device which can establish fluidcommunication with minimal risk of blood leakage during the implantationprocedure, and whilst providing support to the anatomical walls andtissues so as to prevent injury to the patient.

The invention claimed is:
 1. An intracorporeal device for supportingheart function of a patient, wherein said device is configured to besecured across at least two anatomical walls of the heart.
 2. Theintracorporeal device according to claim 1, wherein at least oneanatomical wall is an intra-cardiac wall and a least one anatomical wallis an extra-cardiac wall.
 3. The intracorporeal device according toclaim 1, wherein the intracorporeal device is configured to be securedto one or more anatomical walls by means of: a connector, said connectorarranged to be positioned across one or more anatomical walls; and,optionally, a fixing means, said fixing means being integrally formed orcoupled to the intracorporeal device.
 4. The intracorporeal deviceaccording to claim 3, wherein the fixing means comprises a plurality ofarms extending from the intracorporeal device.
 5. The intracorporealdevice according to claim 1, wherein the intracorporeal device comprisesone or more recesses adapted and configured to receive one or moreanatomical walls.
 6. The intracorporeal device according to claim 1,comprising a proximal portion positioned in a first anatomicalcompartment, an intermediate portion positioned in a second anatomicalcompartment, a distal portion positioned in a third anatomicalcompartment.
 7. The intracorporeal device according to claim 6,comprising a motor located in the proximal portion, one or more fluidinlet ports in the intermediate portion, a pump in the intermediateportion, and one or more fluid outlet ports in the distal portion. 8.The intracorporeal device according to claim 7, wherein the pumpcomprises an impeller and a pump housing, wherein the impeller ispositioned within the pump housing.
 9. The intracorporeal deviceaccording to claim 8, wherein the impeller comprises a tapered profilethat is at a maximum at a central portion of the impeller.
 10. Theintracorporeal device according to claim 7, comprising a static diffuserpositioned in the distal portion and prior to the one or more fluidoutlet ports.
 11. The intracorporeal device according to claim 6,comprising a coupling member at an end of the distal portion.
 12. Theintracorporeal device according to claim 11, wherein the coupling membercomprises a static diffuser.
 13. The intracorporeal device of claim 11,wherein the coupling member facilitates coupling of a fixing means. 14.The intracorporeal device according to claim 10, wherein the staticdiffuser is positioned between the impeller and the one or more fluidoutlet ports.
 15. The intracorporeal device according to claim 7,comprising a motor coupling element that is arranged to couple a driveshaft of the motor to the pump.
 16. The intracorporeal device accordingto claim 15, wherein the motor coupling element magnetically couples thedrive shaft of the motor to the pump.
 17. The intracorporeal deviceaccording to claim 16, wherein the motor coupling element axiallycouples the drive shaft of the motor to the pump.
 18. The intracorporealdevice according to claim 16, wherein the motor coupling elementradially couples the drive shaft of the motor to the pump.
 19. Theintracorporeal device according to claim 15, wherein the motor, thedrive shaft and a magnetic element at an end of the drive shaft aresituated in a hermetically sealed housing.
 20. The intracorporeal deviceaccording to claim 19, wherein a portion of the motor coupling elementsurrounds a portion of the hermetically sealed housing containing themagnetic element.
 21. The intracorporeal device according to claim 20,wherein an interstitial space is present between the portion of themotor coupling element and the portion of the hermetically sealedhousing.
 22. The intracorporeal device of claim 15, wherein an interfaceof the motor coupling element is magnetically fixable to an interface ofthe motor in order to couple the drive shaft to the pump, and wherein agap is present between the interfaces during coupling.
 23. Theintracorporeal device according to claim 22, wherein in use the gapfacilitates fluid flow between the motor interface and the interface ofthe motor coupling element.
 24. The intracorporeal device according toclaim 22, wherein a further interface of the motor coupling elementcouples to an interface of the impeller.
 25. The intracorporeal deviceaccording to claim 15, wherein the motor coupling element comprises oneor more bore portions.
 26. The intracorporeal device according to claim25, wherein the one or more bore portions comprise bore holes thatextend through the motor coupling element.
 27. The intracorporeal deviceaccording to claim 25, wherein the one or more bore portions comprisesegmented arms that couple said interfaces of the motor coupling elementto the respective impeller interfaces.
 28. The intracorporeal deviceaccording to claim 25, wherein in use fluid is arranged to flow betweenthe motor interface and the interface of the motor coupling element andthrough the one or more bore portions towards the impeller.
 29. Theintracorporeal device according to claim 25, wherein the one or morefluid inlet ports are positioned between the one or more bore portionsand the impeller.
 30. The intracorporeal device according to claim 7,wherein the motor comprises power and control means.
 31. Theintracorporeal device according to claim 30, wherein the power andcontrol means is coupled to the motor via a tapered portion.